Differential fluid parameter determination

ABSTRACT

Methods and apparatuses for determining a fluid parameter in a vessel by altering a property of the fluid, sensing the difference in the property after the fluid is altered, particularly as related to the property in an unaltered portion of the fluid.

RELATED APPLICATIONS

This patent application is a continuation of U.S. patent applicationSer. No. 10/238,164 filed Sept. 10, 2002 now U.S. Pat. No. 6,614,212;which is a continuation of U.S. patent application Ser. No. 09/563,107filed May 2, 2000, now U.S. Pat. No. 6,452,371; which is a continuationof U.S. patent application Ser. No. 09/220,139 filed Dec. 23, 1998, nowU.S. Pat. No. 6,075,367; which is a continuation of U.S. patentapplication Ser. No. 08/876,445 filed Jun. 16, 1997, now U.S. Pat. No.5,900,726; which was a continuation of U.S. patent application Ser. No.08/486,982 filed Jun. 7, 1995, now U.S. Pat. No. 5,644,240; which was acontinuation-in-part of U.S. patent application Ser. No. 08/332,647filed Nov. 1, 1994, now U.S. Pat. No. 5,510,716; which was acontinuation of U.S. patent application Ser. No. 07/954,584 filed Sept.30, 1992, now abandoned.

FIELD OF THE INVENTION

This invention relates to measurement of multiple hemodynamic variables.More particularly, this invention relates to measurement of thehemodynamic variables during a medical procedure or for diagnosticpurposes using a differential conductivity monitor to measure or detectat least one of recirculation efficiency, flow rate or the presence ofair bubbles.

BACKGROUND OF THE INVENTION

In many medical situations it is desirable to quantitatively determine,or measure, various hemodynamic parameters, such as the recirculationrate or the recirculation efficiency of a biological or medical fluid toincrease the benefits of, or decrease the time required for, atherapeutic treatment, or for diagnostic purposes. For example,hemodialysis (herein “dialysis”) is an inconvenient, expensive, anduncomfortable medical procedure. It is, therefore, widely recognized asdesirable to minimize the amount of time required to complete theprocedure and to achieve a desired level of treatment.

In dialysis, a joint is typically surgically created between a vein andan artery of a patient undergoing dialysis. The joint provides a bloodaccess site where an inlet line to a dialysis apparatus and an outletline from the dialysis apparatus are connected. The inlet line drawsblood to be treated from the patient, while the outlet line returnsblood to the patient.

The joint may be an arteriovenous fistula, which is a direct connectionof one of the patient's veins to one of the patient's arteries.Alternatively the joint may be a synthetic or animal organ graftconnecting the vein to the artery. As used herein, the term “fistula”refers to any surgically created or implanted joint between one of thepatient's veins and one of the patient's arteries, however created.

In the fistula a portion of the treated blood returned to the patient bythe outlet line may recirculate. Recirculating treated blood willco-mingle with untreated blood being withdrawn from the patient by theinlet line. This recirculated, and the resulting co-mingling of treatedand untreated blood, is dependent, in part, on the rate at which bloodis withdrawn from and returned to the patient. The relationship istypically a direct, but non-linear relationship. It can be readilyappreciated that the dialysis apparatus will operate most effectively,and the desired level of treatment achieved in the shortest period oftime, when the inlet line is drawing only untreated blood at the maximumflow rate capability of the dialysis apparatus consistent with patientsafety. As a practical matter, however, as flow rate through thedialysis apparatus is increased, the proportion of recirculated treatedblood in the blood being drawn through the inlet line is increased. Inorder to select the flow rate through the dialysis apparatus, it isdesirable to know the proportion of recirculated treated blood in theblood being withdrawn from the patient by the inlet line. Thisproportion is referred to herein as the “recirculation ratio”. Therecirculation ratio can also be defined as the ratio between the flow ofrecirculated blood being withdrawn from the fistula to the flow of bloodbeing returned to the fistula. Recirculation efficiency may then bedefined by the relationship:E=1−R  (Equation 1)where

-   -   E=Recirculation efficiency    -   R=Recirculation ratio        Alternatively, recirculation efficiency may be equivalently        expressed as the ratio of blood flow being returned to the        fistula, but not being recirculated, to the total blood flow        being returned to the fistula. Knowing the recirculation        efficiency, the dialysis apparatus operator can adjust the flow        rate through the dialysis apparatus to minimize the time        required to achieve the desired level of treatment.

In the prior art, quantitative determination of recirculation ratio orrecirculation efficiency has typically required laboratory testing, suchas blood urea nitrogen tests, which take considerable amounts of timeand which require withdrawing blood from the patient, which isrecognized as undesirable.

A method and apparatus for qualitatively detecting the presence orabsence of recirculation in a fistula is described in “FAM 10 FistulaFlow Studies and their Interpretation” published by Gambro, Ltd. basedon research performed in 1982. The Gambro method and apparatus injects aquantity of a fluid having an optical density less than the opticaldensity of treated blood into the dialysis apparatus outlet line. Aresulting change in the optical density of the blood being drawn throughthe dialysis apparatus inlet line is qualitatively detected asindicative of the presence of recirculation. The Gambro method andapparatus does not quantitatively determine or measure a recirculationratio or recirculation efficiency.

Devices which qualitatively determine recirculation by thermaltechniques are also known.

A quantitative measurement of the recirculation efficiency of a bodilyor medical fluid is useful in other therapeutic and diagnosticprocedures as well. For example, recirculation ratios and efficienciesare useful for determining cardiac output, intervascular recirculation,recirculation in non-surgically created access sites, and dialyzerperformance from either the blood side or the dialysate side of thedialyzer, or both.

It is known that the electrical conductivity of a fluid in a closednon-metallic conduit can be measured without contact with the fluid byinducing an alternating electrical current in a conduit loop comprisinga closed electrical path of known cross sectional area and length. Themagnitude of the current thus induced is proportional to theconductivity of the fluid. The induced current magnitude may then bedetected by inductive sensing to give a quantitative indication of fluidconductivity. A conductivity cell for measuring the conductivity of afluid in a closed conduit without contact with the fluid is described inU.S. Pat. No. 4,740,755 entitled “Remote Conductivity Sensor HavingTransformer Coupling In A Fluid Flow Path,” issued Apr. 26, 1988 toOgawa and assigned to the assignee of the present invention, thedisclosure of which is hereby incorporated herein by reference.

It is further desirable to have a way of detecting the presence of airin a dialysis apparatus outlet line to minimize the probability of airbeing returned to a patient in the outlet line. It is furtheradvantageous to have a means of determining a volume flow rate of fluidflowing in the inlet and outlet tube of the dialysis apparatus.

Air bubble detectors which detect the presence of an air bubblesonically, ultrasonically or optically are known, but a more sensitivedevice that is not subject to sonic or optical shadows or distortion isdesirable.

It is further desirable to measure a flow rate of a fluid in a tube,either as a part of a recirculation monitoring procedure, or as aseparately measured hemodynamic parameter.

It is still further desirable to provide a hemodymamic monitoring devicewhich is capable of monitoring more than one hemodynamic parameter, inorder to reduce system cost and increase system flexibility.

It is against this background that the differential conductivityhemodynamic monitor of the present invention developed.

SUMMARY OF THE INVENTION

A significant aspect of the present invention is a method and anapparatus for accurately measuring a volumetric flow rate of a fluidflowing in a tube. In accordance with this aspect of the invention thefluid has an electrical conductivity and a corresponding concentrationof conductivity producing ions. The electrical conductivity of the fluidis altered, as by injection of a bolus of hypertonic saline solution.The altered electrical conductivity is measured and integrated overtime. The integrated value is then interpreted to determine flow rate.

Further in accordance with this aspect of the invention, fluidconductivity is measured by flowing the fluid through a conductivitycell with a continuous path configuration, inducing an electricalcurrent in the fluid in the conductivity cell, and sensing the firstelectrical current in the first fluid in the first conductivity cell.Still further in accordance with this aspect of the invention, currentinducing and sensing may be performed by positioning an excitingelectromagnetic coil in proximity with the conductivity cell to inducethe electrical current in the continuous path of the conductivity cell,and positioning a sensing electromagnetic coil in proximity with theconductivity cell to sense the induced current. Yet further inaccordance with this aspect of the invention, the effects of backgroundconductivity are compensated for.

Still further in accordance with this aspect, a second fluid may beflowing in another tube, and the conductivity measuring may measure thedifference between the conductivity of the first fluid in the tube andthe conductivity of the second fluid in the other tube.

A further significant aspect of the present invention is an apparatuscapable of performing a plurality of hemodynamic parameterdeterminations. In accordance with this aspect of the invention theapparatus measures the flow rate of a fluid in a tube and further issuitable for use as a recirculation monitor for determining a degree ofrecirculation of a fluid in a zone of a vessel.

BRIEF DESCRIPTION OF THE DRAWINGS

FIG. 1 is a schematic diagram of a dialysis system incorporating adifferential conductivity recirculation monitor in accordance with thepresent invention.

FIG. 2 is a partial perspective view illustrating the functionalelements of the differential conductivity recirculation monitor shown inFIG. 1.

FIG. 3 is an electrical schematic diagram of the differentialconductivity recirculation monitor shown in FIG. 2.

FIG. 4 is an electrical block diagram of sensing logic usable with thedifferential conductivity recirculation monitor illustrated in FIGS. 2and 3.

FIG. 5 is a graph illustrating differential conductivity versus timeduring a recirculation test employing the differential conductivityrecirculation monitor shown in FIG. 2.

FIG. 6 is a graph illustrating the integral of differential conductivityversus time during a recirculation test employing the differentialconductivity recirculation monitor shown in FIG. 2, having substantiallythe same time scale as FIG. 5.

FIG. 7 is a partial elevational view of a tubing set and sectional viewof an excitation and sensing unit for use with the dialysis system shownin FIG. 1, incorporating the differential conductivity recirculationmonitor in accordance with the present invention.

FIG. 8 is a partially diagrammatic sectional view taken substantially atline 8—8 in FIG. 7.

FIG. 9 is a partially diagrammatic perspective view of the excitationand sensing unit of the differential conductivity recirculation monitorof the present invention.

FIG. 10 is a diagrammatic representation of the passage of an idealbolus of saline and an actual bolus of saline through a conductivitycell of the present invention.

FIG. 11 is an illustration of the output signals from the conductivitycell of FIG. 10.

DETAILED DESCRIPTION OF THE PREFERRED EMBODIMENT

FIG. 1 illustrates a dialysis system 20 incorporating a differentialconductivity recirculation monitor 22 for determining and displayingrecirculation efficiency in accordance with the present invention. Thedialysis system 20, which is one example of a medical system with whichthe present invention may be advantageously used, comprises a dialysisapparatus 24 connected to a fistula 26 surgically formed in a dialysispatient (not shown). Untreated blood is drawn from the fistula 26through a dialyzer inlet needle 28 and a dialyzer inlet line 30. Treatedblood is returned to the fistula through a dialyzer outlet line 32 and adialyzer outlet needle 34. The recirculation monitor 22 is located inthe dialyzer inlet and outlet lines 30 and 32 at a point intermediatebetween the fistula 26 and the dialysis apparatus 24.

The dialysis apparatus 24 comprises a blood pump 36 typically aperistaltic pump, a dialyzer 38 having a blood compartment 40 and adialysate compartment 42 separated by a semi-permeable membrane 44, abubble trap 46 and a dialysate generator 48. Blood is drawn from thefistula 26 by the action of the blood pump 36 and passed through theblood compartment 40 of the dialyzer 38. The membrane 44 allows transferof impurities in the blood, such as urea and creatinine, from the bloodcompartment 40 to the dialysate compartment 42 of the dialyzer 38. Thedialysate compartment 42 is connected to a dialysate generator 48 whichgenerates the dialysate, a liquid isotonic to blood, and circulates itthrough the dialysate compartment 42.

The principles of operation of the differential conductivityrecirculation detector 22 of the present invention are explained inconjunction with FIGS. 2 and 3. The recirculation detector 22 comprisesa needle access site 50 in the dialyzer outlet line 32. A first oroutlet conductivity cell 52 is located in the dialyzer outlet line 32downstream of the needle access site 50. A second or inlet conductivitycell 54 is located in the dialyzer inlet line 30. The first conductivitycell 52 comprises an upstream connection 56, a downstream connection 58and first and second tubing branches 60 and 62, respectively, each ofwhich interconnect the upstream connection 56 with the downstreamconnection 58. Treated blood from the dialyzer flows in the dialyzeroutlet line 32 through the needle access site 50 to the upstreamconnection 56. At the upstream connection 56 the flow splitsapproximately equally with a portion of the treated blood flowing ineach of the two tubing branches 60 and 62 of the outlet conductivitycell 52. The flow rejoins at the downstream connection 58 and flowsthrough the dialyzer outlet line 32 to the fistula 26 (FIG. 1).Similarly, the inlet conductivity cell 54 comprises an upstreamconnection 64, a downstream connection 66 and third and fourth tubingbranches 68 and 70, respectively, which each connect the upstreamconnection 64 to the downstream connection 66. Untreated blood from thefistula 26 flowing in the dialyzer inlet line 30, enters the inletconductivity cell 54 at the upstream connection 64 divides approximatelyequally between the third and fourth tubing branches 68 and 70 andrejoins at the downstream connection 66 to the inlet conductivity cell54. Each one of the tubing branches 60, 62, 68 and 70 has the same crosssectional area and length as each other one of the tubing branches.

The blood, or other biological or medical fluid, flowing in eachconductivity cell 52 and 54 comprises an electrical circuit. Theelectrical circuit is a path for circulation of an electrical currentfrom the upstream connection, through one of the tubing branches, to thedownstream connection and from the downstream connection through theother one of the tubing branches to the upstream connection.

The outlet conductivity cell 52 and the inlet conductivity cell 54 arepositioned adjacent to each other in an angular relationship resemblinga pretzel so that the first tubing branch 60 of the outlet conductivitycell 52 is positioned parallel to the third tubing branch 68 of theinlet conductivity cell at an excitation location. The conductivitycells are further positioned so that the second tubing branch 62 of theoutlet conductivity cell 52 crosses the fourth tubing branch 70 of theinlet conductivity cell 54 at an angle, approximately sixty degrees inthe preferred embodiment, at a sensing location. An excitation coil 72encircles the first tubing branch 60 of the outlet conductivity cell 52and the third tubing branch 68 of the inlet conductivity cell 54 at theexcitation location. A sensing coil 74 encircles the second tubingbranch 62 of the outlet conductivity cell 52 and the fourth tubingbranch 70 of the inlet conductivity cell 54 at the sensing location.

An electrical circuit, as is illustrated schematically in FIG. 3, isthus formed. The excitation coil 72 is inductively coupled to the outletconductivity cell 52 and the inlet conductivity cell 54. When a sourceof excitation energy 76 causes an alternating excitation current,illustrated by direction arrow 78, to flow in the excitation coil 72 achanging magnetic field is generated which causes an electrical current,illustrated by the direction arrow 80, to flow in the blood in theoutlet conductivity cell 52 and causes another electrical current,illustrated by direction arrow 82, to flow in the same electricaldirection in the blood in the inlet conductivity cell 54. Since theconductivity cells 52 and 54 are formed to create electrical paths ofequal cross sectional area and equal path length the electricalconductance of the paths, as illustrated by the schematic resistors 84and 86, and thus the magnitude of the induced currents 80 and 82, willbe related to the conductivity of the blood in the respectiveconductivity cells 52 and 54.

The induced currents 80 and 82 flowing in the outlet and inletconductivity cells 52 and 54 generate a changing magnetic field at thesensing location that induces a sensed current, illustrated by directionarrow 88, in the sensing coil 74. The induced currents 80 and 82 are inopposite electrical directions so that the magnetic field at the sensinglocation has a magnitude proportional to the difference between theinduced currents. The sensed current 88 is proportional to the magneticfield at the sensing location where the sensing coil 74 encircles thesecond and fourth tubing branches 62 and 70, respectively. The sensedcurrent 88 induced in the sensing transformer 74 is thereforeproportional to a difference between the induced currents 80 and 82 inthe outlet and inlet conductivity cells 52 and 54, respectively. Theinduced currents 80 and 82 in the outlet and inlet conductivity cells 52and 54, respectively, are related to the conductivity of the fluids inthose chambers. Therefore, the magnitude of the sensed current 88induced in the sensing coil 74 will be related to the difference betweenthe conductivities of the fluids in the outlet and inlet conductivitycells 52 and 54. The sensed current 88 is delivered to, and interpretedby a sensing logic and display circuit 90, which displays therecirculation efficiency.

It should be appreciated that the present invention will function insubstantially the same way if the locations of the exciting coil 72 andsensing coil 74 are reversed.

Referring now to FIGS. 1 and 2, to use the recirculation monitor 22 toperform a recirculation test the dialysis system operator injects abolus of a marker fluid into the treated blood in the dialyzer outletline 32 at the needle access site 50 using a typical hypodermic needle92. The marker fluid may have an electrical conductivity that is higheror lower than the fluid flowing in the outlet line 32. In the preferredembodiment a high conductivity marker fluid is used to avoid damagingblood cells. In the preferred embodiment the bolus is 1 milliliter of 24percent hypertonic saline solution. The conductivity of the treatedblood being returned to the patient through the dialyzer outlet line 32and the outlet conductivity cell 52 of the recirculation monitor 22 isaltered. This altered conductivity blood enters the fistula through theoutlet needle 34.

If the flow balance in the fistula 26 is such that no flow isrecirculating the altered conductivity blood will exit the fistula, asillustrated by the flow circulation arrow 94, without altering theconductivity of the blood within the fistula. If, however, the flowbalance within the fistula 26 is such that blood is recirculating, asillustrated by flow circulation arrow 96, a portion of the bloodwithdrawn from the fistula 26 by the pump 36 will be the alteredconductivity blood. The recirculation monitor 22 measures theconductivity of the blood flowing in the outlet line 32 and theconductivity of the blood flowing in the inlet line 30 andquantitatively determines the difference between those conductivitiescontinuously throughout the recirculation test. The sensing logic anddisplay circuit 90 interprets the quantitative conductivity differencesmeasured by the recirculation monitor 22 to determine recirculationefficiency.

The determination of recirculation efficiency will be explained byreference to FIGS. 4, 5 and 6. The outlet conductivity cell 52 and theinlet conductivity cell 54 may be thought of as signal generatorsgenerating the induced currents 80 and 82 in the outlet and inletconductivity cells. The induced current 82 of the inlet conductivitycell 54 is inverted 98 and added 100 to the induced current 80 in theoutlet conductivity cell 52, by virtue of the physical relationshipsbetween the conductivity cells, excitation coil 72 and sensing coil 74,to produce the sensed current 88.

The sensing logic and display circuit 90 performs a zeroing operation102, a dialyzer outlet flow determining operation 104, andunrecirculated flow determining operation 106, and a dividing operation108, and includes a visual display device 110, preferably a liquidcrystal display. Alternatively the functions of the sensing logic anddisplay circuit 90 may be performed by a digital computer (not shown).

FIG. 5 is a graph illustrating differential conductivity (reference 112)as a function of time (reference 114) during a typical recirculationtest. FIG. 6 is a graph illustrating the integral of differentialconductivity (reference 116) as a function of time 114 during thetypical recirculation test. Prior to the beginning of the recirculationtest there may be some normal difference (reference 118) between theconductivity of the treated blood in the dialyzer outlet line 32 (FIG.2) and the untreated blood in the dialyzer inlet line 30 (FIG. 2). Thisnormal conductivity difference 118 is subtracted from the sensed current88 by the zeroing operation 102 of the sensing logic and display circuit90 to remove the effect of the normal difference in conductivity 118from determination of recirculation efficiency. The recirculation testbegins (reference time T1) when the bolus of high conductivity fluid isinjected into the dialyzer outlet line 32 (FIG. 2) at the needle accesssite 50 (FIG. 2). The conductivity of the treated blood in the dialyzeroutlet line 32 (FIG. 2) is increased. As the bolus passes through theoutlet conductivity cell 52 (FIG. 2) the differential conductivity 112increases (reference 120) and then decreases (reference 122) until thenormal conductivity difference 118 is reached (reference time T2). Theoutlet flow determining operation 104 calculates the integral ofconductivity from the start of the test (reference time T1) until thedifferential conductivity returns to the normal value 118 (referencetime T2). The integral 116 of the conductivity increases (reference 124)until a first steady state value (reference 126) of the integral 116 isreached when the differential conductivity 112 returns to the normalvalue 118 (reference time T2). The first steady state value 126 isstored by the outlet flow determining operation 104 and isrepresentative of the flow of treated blood in the dialyzer outlet line32 (FIG. 2).

After the treated blood with the altered conductivity enters the fistula26 (FIG. 1) a portion of it may recirculate and be withdrawn from thefistula 26 (FIG. 1) through the dialyzer inlet line 30 (FIG. 2). Theconductivity of the untreated blood in the inlet conductivity cell 54 isincreased (reference time T3), causing the differential conductivity todecrease 128 and then increase 130, returning to the normal value ofconductivity difference 118 (reference time T4). The integral ofdifferential conductivity from the beginning of the recirculation test(reference time T1) until the normal value of conductivity difference118 is reached again (reference time T4) is calculated by theunrecirculated flow determining operation 106 of the sensing logic anddisplay circuit 90. The integral of differential conductivity 116decreases (reference) to a second steady state value 134 (reference timeT4.

The second steady state value 134 of the integral of differentialconductivity is stored by the unrecirculated flow determining operation106 of the sensing logic and display circuit 90 and is representative ofthe portion of the bolus of high conductivity liquid that was notrecirculated. The second steady state value 134 is thus representativeof the unrecirculated portion of the treated blood flow. The dividingoperation divides the second steady state value 134 by the first steadystate value 126 to calculate a recirculation efficiency 136. Therecirculation efficiency 136 is provided to the operator as a visualoutput by the display device 110.

It will be apparent to those skilled in the art that the sensing logicand display circuit 90 may be implemented using analog or digitalcircuit devices and that other calculation algorithms may be used tocalculate recirculation efficiency 138. Further, the recirculationefficiency 138 may be calculated in real time or, alternatively, thenecessary data stored and the calculations performed on the stored data.

Further details of the preferred embodiment of the differentialconductivity recirculation monitor will be explained by reference toFIGS. 7-11.

FIG. 7 illustrates a portion of a typical disposable tubing set 140incorporating conductivity cells 52 and 54 in accordance with thepresent invention. As is well known in the art, it is highly desirablefor all portions of the tubing set 140 to be used with a dialysis systemto be disposable, in order to prevent cross contamination and infectionbetween patients. This is true of most blood and other biological ormedical fluid processing systems.

Disposable tubing sets may be formed from a plurality of plastic tubes,connectors, needles and medical devices using techniques that are wellknown in the art. The discussion of the tubing set 140 will therefore belimited to a discussion of the differential conductivity recirculationmonitor 22 (FIG. 1) portion of the tubing set.

The dialyzer outlet line 32 is a plastic tube which extends through theneedle access site 50, into the outlet conductivity cell 52. The outletconductivity cell 52 comprises a plastic conduit loop and includes theupstream connection 56, elongated divided first and second tubingbranches 60 and 62, and the downstream connector 58. The downstreamconnector 58 has mounted in it an extension of the dialyzer outlet line32, which is mounted through a connector 142 to the outlet needle 34.

The dialyzer inlet needle 28 is connected through a connector 144, tothe dialyzer inlet line 30. The dialyzer inlet line 30 is connected tothe inlet conductivity cell 54, which includes the upstream connection64, elongated divided third and fourth tubing branches 68 and 70respectively, and downstream connector 66. The dialyzer inlet line 30extends from the downstream connector 66 to the dialyzer apparatus 24(FIG. 1).

In the preferred embodiment the portion of the dialyzer outlet line 32between the dialyzer outlet needle 34 and the downstream connector 58 ofthe outlet conductivity cell 52 and the portion of the dialyzer inletline 30 between the dialyzer inlet needle 28 and the upstream connector64 of the inlet conductivity cell 54 must be sufficiently long so thatthe bolus of marker fluid passes completely through the outletconductivity cell before any altered conductivity fluid from the fistula26 enters the inlet conductivity cell.

The conductivity cells 52 and 54 have the overall shape of links in anordinary chain, straight side portions 146 being joined at their ends bysemicircular portions 148. In cross-section at the excitation location,as shown in FIG. 8, the wall of each conductivity cell 42 and 54 definesa D, the insides of the Ds providing conduit portions 150 and 152. Aflat portion 154 of the D of the outlet conductivity cell 52 is abuttedand adhered to a flat portion 156 of the D of the inlet conductivitycell 54 along one pair of semicircular portions 148 of the conductivitycells. The other pair of circular portions 148 are separated so thataxes of the conductivity cells 52 and 54 define therebetween an angle ofapproximately sixty degrees. The flat portions 154 and 156 of theconductivity cells 52 and 54 are further joined along two of thestraight portions 146 at a location along the second and fourth tubingbranches 62 and 70, respectively at the sensing location. An orientationtab 159 is formed on the inlet conductivity cell 54.

Mating with tube set 140 is a tubing set acceptor 160. As shown in FIG.9, the tubing set acceptor 160 comprises a portion of an excitation andsensing unit 162 which also includes a logic circuit module 164. Thetubing set acceptor 160 comprises a portion of a first, or rear,acceptor plate 166 and a second, or front, acceptor plate 168 joined bya hinge 169 for motion between open and closed positions and providedwith a latch or spring (not shown) to hold the acceptor plates in theclosed position. The first acceptor 166 plate is relieved to accept intoappropriately-shaped indentations 170 thereof the outlet conductivitycell 52 (FIG. 2) and portions the tubing set 140 (FIG. 7). The secondacceptor plate 168 is relieved to accept into appropriately-shapedindentations 172 thereof the inlet conductivity cell 54 and portions ofthe tubing set 140 (FIG. 7). An orientation tab recess 173 is defined byat least one of the appropriately shaped indentations 170 and 172. Theorientation tab recess 173 cooperates with the orientation tab 159 (FIG.7) of the tubing set 140 (FIG. 7) to assure that the tubing set iscorrectly oriented when installed in the tubing set acceptor 160.

The tubing set acceptor 160 is sufficiently large to support theconductivity cells 52 and 54 and enough of the dialyzer outlet line 32and dialyzer inlet line 30 so that fluid flow patterns through theconductivity cells are substantially repeatable, being relativelyunaffected by bends, curves, tubing movement, and other disturbances orvariations in the positions of the outlet and inlet lines with respectto the conductivity cells during measurement.

The excitation coil 72 and sensing coil 74 are mounted to the tubing setacceptor 160. The excitation coil 72 and sensing coil, 74 are positionedat right angles to each other to minimize magnetic interference betweenthe coils. The excitation coil 72 comprises a first, or rear, and asecond, or front, half core 174 and 176, respectively. Similarly thesensing coil comprises a third, or rear, and a fourth, or front,half-core 178 and 180 respectively. The first and third half-cores 174and 178, respectively are mounted to the first acceptor plate 166 andthe second and third half cores 176 and 180 respectively are mounted tothe second acceptor plate 186.

As illustrated in FIG. 8, each half core has a U-shaped configuration,with short legs 182 having ends 184 and connecting legs 186. The tubingset acceptor 160 holds a portion of the tubing set 140 which includesthe conductivity cells 52 and 54 in a fixed relationship with theexcitation coil 72 and sensing coil 74.

The first and second half cores 174 and 176 are oriented so that theirends 184 abut when the first and second acceptor plates 166 and 168 arebrought to the closed position. The excitation coil 72 thus formed is inthe shape of a rectangle defining a rectangular window. The third andfourth half cores 178 and 180 are similarly oriented so that their endsabut when the first and second acceptor plates 166 and 168 are broughtto the closed position. The sensing coil 74 thus formed is also in theshape of a rectangular ring defining a rectangular window (not shown).When a tubing set 140 is placed in the tubing set acceptor 160 the firstand third tubing branches 60 and 68 are engaged in the window of theexcitation coil 72 and the second and fourth tubing branches 62 and 70are engaged in the window of the sensing coil 74 so that the coilsencircle the corresponding tubing branches. Biasing springs 188 may beprovided to hold corresponding half-cores in firm contact when theacceptor plates 166 and 168 are closed.

The legs 182 and 186 of the coil 72 and 74 are square in cross-section.At least one connecting leg 186 of each coil 72 and 74 is transformerwire wrapped 190.

The logic circuit module 164 of the excitation and sensing unit 162 maybe mounted to one of the acceptor plates 168 or may be separate from thetubing set acceptor 160 with wiring interconnections (not shown) to thetubing set acceptor 160. Further, either or both of the logic circuitmodule 164 or the tubing set acceptor 160 may be incorporated into thedialysis apparatus 24. The logic circuit module houses the sensing logicand display circuit 90, with the display device 110 and one or moremanual input switches 192 to enable the operator to perform suchfunctions as turning the recirculation monitor on and off, testing theoperation of the monitor and initiating recirculation test, and may alsoinclude switches and displays associated with other hemodynamicmonitoring functions.

Although the display device 110 and manual input switches 192 are shownin FIG. 9 as being on a side 194 of the logic circuit module 164adjacent to the second acceptor plate 168, in the preferred embodimentthe display device and manual input switches may be on a side 196opposite the second acceptor plate 168, or any other side of the logiccircuit module.

The circuitry for conductivity measurement and calibration may suitablybe as set forth in the Ogawa patent incorporated by reference above.

The apparatus and methods described above may optionally be adapted tomeasure and detect other hemodynamic parameters such as the presence ofentrained air in the treated blood returned to the patient from thedialysis apparatus 24 through the dialyzer outlet line 32. For this useit is not necessary to inject saline at the needle access site 50.Entrained air in the blood in the form of a large bubble will cause anelectrical discontinuity in the outlet conductivity cell 52 as it passesthrough either of the tubing branches 60, 62 of the outlet conductivitycell 52. This will cause the magnitude of induced current 80 flowing inthe outlet conductivity cell 52 to be greatly reduced or turned offcompletely, depending on the size of the bubble. Further, a plurality ofsmall bubbles will effectively reduce the conducting volume of the bloodin the tubing branches 60, 62 of the conductivity cell, decreasing theconductance, and therefore the induced current 80, in the outletconductivity cell 52.

By sensing this reduction in the outlet conductivity cell 52 inducedcurrent 80 the passage of a bubble or a plurality of bubbles can bedetected, and corrective action taken, if necessary, to minimize theirintroduction into the patient through the outlet line 32 and outletneedle 28. Corrective action may include turning off the dialysisapparatus 24, closing a venous clamp (not shown) and/or activatingindicator or alarm devices to alert a human operator of the presence ofthe air bubble of bubbles.

In the preferred embodiment, a difference in the conductivity of theblood in the outlet conductivity cell 52 of the outlet line 32 and theblood in the inlet conductivity cell of the inlet line 30 issubstantially constantly monitored. When one or more air bubbles enterthe outlet conductivity cell 52, causing the conductance, and thus theinduced current 80 and resulting sensed conductivity of the fluid in thecell 52, to decrease relative to the conductivity of the blood in theinlet conductivity cell 54, this decrease is sensed by logic in thesensing logic and display circuit 90 of the logic circuit module 164 ofthe excitation and sensing unit 162. If the conductivity of the blood inthe outlet conductivity cell 52 is sufficiently lower than theconductivity of the blood in the inlet conductivity cell 54, thisconductivity difference is interpreted as the presence of entrained airin the outlet line 32.

The apparatus and methods described above may optionally be adapted tomeasure the hemodynamic parameter of blood volumetric flow in the outletline 32. Blood volumetric flow rate may be measured and displayed as andincident to the measurement of a degree of recirculation, as describedabove, or may be measured in a separate blood volumetric flow monitoringprocedure.

The measurement of blood volumetric flow using the differentialconductivity sensor of the present apparatus will be explained byreference to FIGS. 10 and 11. The conductivity of a fluid is directlyproportional to the concentration of conductivity producing ions in thefluid. Consider an ideal bolus 202 of hypertonic saline solution havinga known volume vol and a known mass of conductivity altering ions M. Theion concentration of this ideal bolus 202 would be: $\begin{matrix}{C = \frac{M}{vol}} & \left( {{Equation}\quad 2} \right)\end{matrix}$If this bolus were injected at the needle access site 50 into the outletline 32, which is a tube of known cross-sectional area a, into fluidflowing at a flow rate Q, corresponding to a velocity V, the ideal boluswould pass through the outlet line 32 in the form of a cylinder having alength L, L being defined as: $\begin{matrix}{L = \frac{vol}{a}} & \left( {{Equation}\quad 3} \right)\end{matrix}$

As this ideal bolus 202 passes through the outlet conductivity cell 52it would cause the conductivity cell to sense a square pulse 204 ofaltered differential conductivity having a magnitude proportional to theion concentration C of the bolus and a duration t₁ proportional to thelength L of the bolus 202 and the flow rate Q of the fluid. The flowrate of the fluid can then be calculated as: $\begin{matrix}{Q = {{Va} = {\frac{La}{t_{1}} = \frac{M}{{Ct}_{1}}}}} & \left( {{Equation}\quad 4} \right)\end{matrix}$Note that Ct₁ is the area under the sensed square pulse 204.

In reality the bolus 202′ of known volume vol and known mass ofconductivity altering ions M will not take the form of a perfectcylinder, but will exhibit gradual leading edge curve 206 and trailingedge curve 208, and will further diffuse into the fluid in the outletline 32. The differential conductivity pulse 204′ caused by the passageof the bolus 202′ through the outlet conductivity cell 52 will deviatesubstantially from a square pulse and will have gradually increasing anddecreasing leading and trailing edges 210, 212 corresponding to theleading and trailing edges 206, 208 of the bolus. Furthermore, the timet₂ that the bolus 202′ takes to pass through the outlet conductivitycell will be longer than the time t₁ for an ideal bolus 202. In order todetermine the flow rate, Q it is necessary to determine the area underthe differential conductivity curve by integrating the output over timeas follows: $\begin{matrix}{Q = \frac{M}{\int_{0}^{t_{2}}{{C(t)}{\mathbb{d}t}}}} & \left( {{Equation}\quad 5} \right)\end{matrix}$

Thus, if a bolus of saline of a known volume vol and a knownconcentration of conductivity altering ions C_(k) is injected into theneedle access site 50, the flow rate of the fluid can be determined tobe: $\begin{matrix}{Q = \frac{C_{k}*{vol}}{\int_{0}^{t_{2}}{{C(t)}{\mathbb{d}t}}}} & \left( {{Equation}\quad 6} \right)\end{matrix}$

When the fluid flowing in the conductivity cell 32 has a backgroundconductivity, representing a background concentration C_(b) ofconductivity, measured by the outlet conductivity cell 52 immediatelyprior to the passage of the bolus 202′ through the cell 52, representinga background level of conductivity producing ions, the effect of thebackground level must be subtracted to obtain the correct value of flow:$\begin{matrix}{Q = \frac{\left( {C_{k} - C_{b}} \right)*{vol}}{\int_{0}^{t_{2}}{\left( {{C(t)} - C_{b}} \right){\mathbb{d}t}}}} & \left( {{Equation}\quad 7} \right)\end{matrix}$In the differential conductivity cell 22 of the preferred embodimentC_(b) is representative of a difference in background concentration, andhence conductivity, between the fluid in the outlet conductivity cell 52and the fluid in the inlet conductivity cell. If, under steady stateconditions, the conductivity of fluid in the outlet cell 52 is the sameas the conductivity in the inlet cell, then the background concentrationC_(b) is zero. The preferred embodiment of the present invention mayoptionally be provided with selectably engageable logic to analyze adifferential conductivity pulse from the bolus 202′ of saline passingthrough the outlet conductivity cell 52 and generate a value indicativeof the flow rate through the conductivity cell. This value may beselectively displayable on the same display device 110 as is used todisplay a degree of recirculation. The bolus of saline 202′ mayoptionally be the same bolus used to determine a degree ofrecirculation, in which case the flow rate will be determinedsubstantially simultaneously with the degree of recirculation anddisplayed simultaneously of sequentially therewith.

The apparatus and methods described above may optionally be furtheradapted to incorporate the capability of measuring or detecting morethan one hemodynamic parameter into a single differential conductivitymeasuring apparatus.

The preferred embodiments of the present invention has been described byreference to determination of recirculation efficiency in a surgicallycreated blood access site during, or in conjunction with, a hemodialysisprocedure. It should be understood that the present invention is not solimited. The present invention may be used in a variety of medical andnon-medical circumstances where it is desirable to determinerecirculation efficiency. Further, it should be understood that thepresent invention may be used in a variety of medical and non-medicalcircumstances where it is desirable to compare the electricalconductivities of two fluids. Presently preferred embodiments of thepresent invention and many of its aspects, features and advantages havebeen described with a degree of particularity. It should be understoodthat this description has been made by way of preferred example, andthat the invention is defined by the scope of the following claims.

1. A method for quantitatively determining a parameter of a fluid havinga physical property, said fluid being disposed in a vessel into whichflows a first portion of said fluid having a first value of saidphysical property, and out of which vessel flows a second portion ofsaid fluid having a corresponding second value of said physicalproperty, said method comprising: altering the first value of saidphysical property of the first portion of said fluid; measuring thedifference between the first and second values of said physicalproperty; and interpreting the difference between the first and secondvalues of said physical property in a manner which provides forquantitatively determining a parameter of said fluid.
 2. A method asdefined in claim 1 wherein: the step of altering the first value of saidphysical property of the first portion of said fluid further comprises:injecting a marker fluid having a value of said physical propertydifferent from the first value of the physical property of the firstportion of said fluid into the first portion of said fluid.
 3. A methodas defined in claim 1 wherein either of the measuring and interpretingsteps further comprise compensating for the effect of the first value ofthe physical property of the first portion of the fluid as the firstvalue of the physical property was prior to the altering step.
 4. Amethod as defined in claim 1 wherein the step of measuring thedifference of the first and second values of said physical propertyfurther comprises: flowing the second portion of said fluid in a secondconduit, the second conduit having a second measuring cell with a secondcontinuous path configuration and measuring the second value of saidphysical property of the second portion of the fluid in the secondmeasuring cell.
 5. A method as defined in claim 1 wherein the step ofmeasuring the difference of the first and the second values of saidphysical property further comprises: flowing the first portion of saidfluid through a first conduit, said first conduit comprising a firstmeasuring cell with a first continuous path configuration; flowing thesecond portion of said fluid through a second conduit, said secondconduit comprising a second measuring cell with a second continuous pathconfiguration; wherein said measuring step includes measuring thedifference between the first value of said physical property in thefirst portion of the fluid in the first measuring cell and the secondvalue of said physical property in the second portion of the fluid inthe second measuring cell; and producing a signal representative of thedifference of the first and second values of said physical property inthe first and the second portions of the fluid.
 6. A method as definedin claim 1 wherein either of the measuring and interpreting stepsfurther comprise compensating for the effects of either of the first andthe second values of said physical property.
 7. A method as defined inclaim 1 wherein the fluid is blood and the first portion of said fluidis treated blood being delivered from a hemodialysis apparatus.
 8. Amethod as defined in claim 1 wherein the fluid is blood and the secondportion of said fluid is untreated blood being delivered to ahemodialysis apparatus.
 9. A method as defined in claim 1 wherein thefluid parameter is a measure of flow.
 10. A method as defined as claim 1wherein the fluid parameter is a measure of recirculation.
 11. A methodas defined in claim 1 wherein the step of measuring the difference ofthe first and second values of said physical property further comprises:flowing the first portion of said fluid through a first conduit, saidfirst conduit comprising a first measuring cell with a first continuouspath configuration; and measuring the first value of said physicalproperty in the first portion of the fluid in the first measuring cell.12. A method as defined in claim 11 wherein said physical property ofsaid fluid is conductivity, and the measuring step further comprises:positioning an inducing device as part of or in proximity with the firstmeasuring cell at an inducing location; and using the inducing device toinduce a first current in first direction along the continuous path ofthe first measuring cell; positioning a sensing device as part of or inproximity with the first measuring cell at a sensing location; andsensing the first current in the first portion of said fluid in thefirst measuring cell.
 13. A method as defined in claim 11 wherein: thestep of altering the first value of said physical property of the firstportion of said fluid further comprises: altering the first value ofsaid physical property of the first portion of said fluid prior to theflowing of said first portion of said fluid through said first measuringcell.
 14. A method as defined in claim 11 wherein: the altering stepfurther comprises: altering the first value of said physical propertyafter the flowing of said first portion of said fluid through the firstmeasuring cell.
 15. An apparatus for quantitatively determining aparameter of a fluid having a physical property, said fluid beingdisposed in a vessel into which flows a first portion of said fluidhaving a first value of said physical property, and out of which vesselflows a second portion of said fluid having a corresponding second valueof said physical property, said apparatus comprising: means for alteringthe first value of said physical property of the first portion of saidfluid; and means for measuring the difference between the first andsecond values of said physical property; and means for interpreting thedifference between the first and second values of said physical propertyto quantitatively determine a parameter of said fluid.
 16. An apparatusas defined in claim 15 wherein: the means for altering the first valueof said physical property of the first portion of said fluid furthercomprises: means for injecting a marker fluid having a value of saidphysical property different from the first value of said physicalproperty of the first portion of said fluid into the first portion ofsaid fluid.
 17. An apparatus as defined in claim 15 wherein either ofthe means for measuring and the means for interpreting further comprisesmeans for compensating for the effect of the first value of saidphysical property of the first portion of the thud as the first value ofsaid physical property was prior to any alteration thereof.
 18. Anapparatus as defined in claim 15 wherein the means for measuring thedifference of the first and second values of said physical propertyfurther comprises: a second conduit through which the second portion ofsaid fluid having the second value of the physical property flows fromthe vessel, the second conduit having a second measuring cell with asecond continuous configuration wherein the means for inducing furthercomprises: means for measuring the second value of the physical propertyin the second portion of said fluid in the second measuring cellfollowing the second continuous path configuration.
 19. An apparatus asdefined in claim 15 wherein the means for measuring the difference ofthe first and the second values of said physical property furthercomprises: a first conduit through which the first portion of said fluidflows to the vessel, said first conduit comprising a first measuringcell with a first measuring cell upstream connection, a first measuringcell downstream connection, and two branches connecting the upstreamconnection to the downstream connection with a first continuous pathconfiguration from the upstream connection to the downstream connectionthrough one of the two branches and returning to the upstream connectionthrough the other one of the two branches; a second conduit throughwhich the second portion of said fluid flows from the vessel, saidsecond conduit comprising a second measuring cell with a secondmeasuring cell upstream connection, a second measuring cell downstreamconnection, and two branches connecting the upstream connection to thedownstream connection with a second continuous path configuration fromthe upstream connection to the downstream connection through one of thetwo branches and returning to the upstream connection through the otherone of the two branches; wherein said means for measuring includesmeasuring the difference between the first value of said physicalproperty of the first portion of said fluid in the first measuring celland the second value of said physical property of the second portion ofsaid fluid flowing in the second measuring cell, and means for producinga signal representative of the difference of the first and second valuesof said physical property of the first and the second portions of saidfluid.
 20. An apparatus as defined in claim 15 wherein: the alteringmeans for altering the value of said first physical property of thefirst portion of said fluid is disposed so as to alter the value of saidfirst physical property of the first portion of said fluid after theflowing of said first portion of said fluid through said first measuringcell.
 21. An apparatus as defined in claim 15 further comprising anapparatus adapted interpreting difference between the first and secondvalues of said physical property for quantitatively determining thedegree of flow recirculation within a vessel.
 22. An apparatus asdefined in claim 15 wherein the fluid is blood and the first portion ofsaid fluid is treated blood being delivered from a hemodialysisapparatus.
 23. An apparatus as defined in claim 15 wherein the fluid isblood and the second portion of said fluid is untreated blood beingdelivered to a hemodialysis apparatus.
 24. An apparatus as defined inclaim 15 wherein the fluid parameter is a measure of flow.
 25. Anapparatus as defined in claim 15 wherein the means for measuring thedifference of the first and second values of said physical property ofthe respective first portion of said fluid and the second portion ofsaid fluid further comprises: a first conduit through which the firstportion of said fluid flows to the vessel, said first conduit comprisinga first measuring cell with a first measuring cell upstream connection,a first measuring cell downstream connection, and two branchesconnecting the upstream connection to the downstream connection with afirst continuous pat configuration from the upstream connection to thedownstream connection through one of the two branches and returning tothe upstream connection through the other one of the two branches; meansfor measuring the first value of said physical property in the firstportion of said fluid in the first measuring cell.
 26. An apparatus asdefined in claim 25 wherein the physical property of said fluid isconductivity; and the measuring means comprises an inducing device aspart of or disposed in proximity with the first measuring cell at aninducing location; and a sensing device as part of or disposed inproximity with the first measuring cell at a sensing location.
 27. Anapparatus as defined in claim 25 wherein: the means for altering theelectrical conductivity of the value of said first physical property ofthe first portion of said fluid is disposed so as to alter said firstphysical property of the first portion of said fluid prior to theflowing of said first portion of said fluid through said first measuringcell.